Multiple reservoir programmable pump

ABSTRACT

Different embodiment programmable pumps including multiple reservoirs are disclosed, as are methods of utilizing same. The pumps generally include at least two reservoirs and means for dispensing active substances housed in each at varying flow rates.

CROSS-REFERENCE TO RELATED APPLICATIONS

The present application is a continuation of U.S. patent application Ser. No. 13/338,593, filed on Dec. 28, 2011, the disclosure of which is hereby incorporated by reference herein.

BACKGROUND OF THE INVENTION

The present invention relates to a multiple reservoir implantable pump that is programmable so as to allow for varying flow rates of active substances from each of the reservoirs to be delivered to a patient.

Implantable pumps have been well known and widely utilized for many years. Typically, pumps of this type are implanted into patients who require the delivery of medication or other fluids (hereinafter referred to as “active substances”) to specific areas of their body. For example, patients that are experiencing severe pain may require pain killers daily or multiple times per day. Absent the use of an implantable pump or the like, a patient of this type would be subjected to one or more painful injections of such active substances. In the case of pain associated with more remote areas of the body, such as the spine, these injections may be extremely difficult to administer and particularly painful for the patient. Furthermore, attempting to treat conditions such as this through oral or intravascular administration of an active substance often requires higher doses and may cause severe side effects. Therefore, it is widely recognized that utilizing an implantable pump may be beneficial to both a patient and the treating physician.

Many implantable pump designs have been proposed. For example, U.S. Pat. No. 4,969,873 (“the '873 patent”), the disclosure of which is hereby incorporated by reference herein, teaches one such design. The '873 patent is an example of a constant flow pump, which typically includes a housing having two chambers, a first chamber for holding the active substance to be administered to the patient, and a second chamber for holding a propellant. A flexible membrane separates the two chambers such that expansion of the propellant in the second chamber pushes the active substance out of the first chamber. This type of pump also typically includes an outlet opening connected to the first chamber on one end and a catheter or other delivery device for directing the active substance to the desired area of the body on the other, a replenishment opening for allowing refilling of the first chamber, and a bolus opening for allowing the direct introduction of an active substance through the catheter without introduction into the first chamber. Both the replenishment and bolus openings are covered by septa that allow a needle or similar device to be passed therethrough, but which seal the openings upon removal of the needle. As pumps of this type provide a constant flow of active substance to the specific area of the body, they must be refilled periodically with a proper concentration of active substance suited for extended release.

Implantable pumps may also be of the programmable type, meaning that they can provide variable flow rates of an active substance therefrom. While these types of programmable pumps have typically involved the use of a solenoid pump or peristaltic pump, certain pumps similar to the above-discussed constant flow pumps have been modified in order to provide the ability of providing varying flow rates of an active substance from the pump. For instance, U.S. Patent Application Publication Nos. 2007/0005044 and 2007/0112328, the disclosures of which are hereby incorporated by reference herein, teach such pumps. However, those pumps are limited to a single active substance chamber.

Implantable pumps having multiple reservoirs are also known in the art. For instance, U.S. Patent Application Publication No. 2006/0271022 (“the '022 Publication”), the disclosure of which is hereby incorporated by reference herein, teaches a multiple reservoir pump design. While that reference also teaches such a multiple reservoir implantable pump that employs a patient controlled actuation mechanism, as well as a method of varying flow rate from the pump by modifying the amounts of active substance included in each of its multiple reservoirs (to allow multiple fixed flow rates), it does not teach a programmable type pump. The benefits of such a programmable pump are widely known from the previous incarnations that included a single active substance chamber. However, heretofore, there have not been any suitable incarnations of such a pump.

Therefore, there exists a need for a programmable multiple reservoir implantable pump.

BRIEF SUMMARY OF THE INVENTION

A first aspect of the present invention is a programmable pump system for dispensing first and second active substances at varying flow rates to a patient. In accordance with one embodiment of this first aspect, the pump system includes a pump housing defining an interior including a first chamber containing the first active substance, a second chamber containing the second active substance, and a third chamber containing a propellant; a first valve in fluid communication with the first chamber; a second valve in fluid communication with the second chamber; and a catheter fluidly connected with the first and second chambers. Preferably, expansion of the propellant within the third chamber causes the first active substance to flow from the first chamber at a first flow rate towards the catheter and the second active substance to flow from the second chamber at a second flow rate towards the catheter, actuation of the first valve varies the first flow rate, and actuation of the second valve varies the second flow rate.

Other embodiments of the first aspect may include a pump where the first and second active substances are identical. The pump may further include first and second membranes defining the third chamber. The housing may include first and second portions, the first and second membranes captured between the first and second portions so that the first portion and first membrane defines the first chamber and the second portion and second membrane defines the second chamber. First and second pressure sensors may be associated with the first chamber and third and fourth pressure sensors associated with the second chamber, wherein a comparison of pressure readings taken by the first and second pressure sensors determines whether the first valve should be actuated and a comparison of pressure readings taken by the third and fourth pressure sensors determines whether the second valve should be actuated.

In still other embodiment, the pump may further include a first motor for actuating the first valve and a second motor for actuating the second valve. The actuation of the first and second valves may occurs in planes parallel to planes of the top and bottom of the pump housing or in perpendicular planes thereof. The pump may further include a first offset cam associated with the first motor and first valve and a second offset cam associated with the second motor and second valve, where rotation of the first offset cam by the first motor causes the first valve to actuate and rotation of the second offset cam by the second motor causes the second valve to actuate. A first lever may be associated with the first motor and first valve and a second lever may be associated with the second motor and second valve, where movement of the first lever by the first motor causes the first valve to actuate and movement of the second lever by the second motor causes the second valve to actuate.

The pump may be configured such that the first and second pressure sensors and first motor are contained within a first hermetic housing and the third and fourth pressure sensors and second motor are contained within a second hermetic housing. Those hermetic housings may be constructed of titanium, and welded together so as to be sealed from fluid and/or gas. The first hermetic housing may include a first aperture covered by a first membrane and the second hermetic housing includes a second aperture covered by a second membrane. The first membrane may be associated with the first motor and the first lever and the second membrane may be associated with the second motor and the second lever.

The pump may also include a third hermetic housing associated with the first and second hermetic housings. The third hermetic housing may include at least one power source and at least one electronic component, such as a processing unit. The pump may include a replenishment opening for use in filling the first chamber with the first active substance and the second chamber with the second active substance. The pump may further include a third valve in fluid communication with the replenishment opening and first and second chambers. When the third valve is in a first position only the first chamber can be refilled and when the third valve is in a second position only the second chamber can be refilled. The pump may include an actuation mechanism for actuating the third valve between the first and second positions.

BRIEF DESCRIPTION OF THE DRAWINGS

A more complete appreciation of the subject matter of the present invention and the various advantages thereof, can be realized by reference to the following detailed description in which reference is made to the accompanying drawings in which:

FIG. 1 is a top perspective view of a multiple reservoir implantable pump in accordance with an embodiment of the present invention.

FIG. 2 is a side view of the implantable pump shown in FIG. 1.

FIG. 3 is a top perspective view of the implantable pump shown in FIG. 1 with a cap removed.

FIG. 4 is a top perspective view similar to the one shown in FIG. 3, with a housing cover removed therefrom.

FIG. 5 is a cross-sectional view of the implantable pump shown in FIG. 1 taken along line A-A.

FIG. 6 is a cross-sectional view of the implantable pump shown in FIG. 1 taken along line B-B.

FIG. 7 is a top perspective view of a lower portion of the implantable pump shown in FIG. 1.

FIG. 8 is a top perspective view of an upper portion of the implantable pump shown in FIG. 1, with certain components removed therefrom.

FIG. 9 is a top view of the upper portion shown in FIG. 8.

FIG. 10 is a perspective view of a component support removed from the implantable pump shown in FIG. 1.

FIG. 11 is a cross-sectional view of the upper portion shown in FIG. 8 taken along line C-C.

FIG. 12 is a bottom perspective view of the upper portion shown in FIG. 8.

FIG. 13 is a partial cross-sectional top view of the implantable pump shown in FIG. 1.

FIG. 14 is a cross-sectional top view of the implantable pump shown in FIG. 1.

FIG. 15 is a partial transparent view of the upper portion shown in FIG. 8

FIG. 16 is a top perspective view of a multiple reservoir implantable pump in accordance with another embodiment of the present invention.

FIG. 17 is a side view of the implantable pump shown in FIG. 16.

FIG. 18 is a top perspective view of a portion of a hermetic housing included in the implantable pump shown in FIG. 16.

FIG. 19 is a bottom perspective view of the hermetic housing shown in FIG. 18.

FIG. 20 is a top perspective view of the hermetic housing shown in FIG. 18, with a cover portion removed

FIG. 21 is a top cross sectional view of the implantable pump shown in FIG. 16 taken along line D-D of FIG. 16.

FIG. 22 is a cross sectional view of the implantable pump shown in FIG. 17 taken along line E-E of FIG. 21.

FIG. 23 is a cross sectional view of the implantable pump shown in FIG. 15 taken along line F-F of FIG. 21.

FIG. 24 is a cross sectional view of the implantable pump shown in FIG. 16 taken along line G-G of FIG. 21.

FIG. 25 is a top cross sectional view of an upper portion of the implantable pump shown in FIG. 16.

FIG. 26 is a top perspective view of the upper portion of the implantable pump shown in FIG. 16.

FIG. 27 is a lower perspective view of the upper portion shown in FIG. 26.

FIG. 28 is a perspective view of a collector manifold.

FIG. 29 is a top view of a multiple reservoir implantable pump in accordance with yet another embodiment of the present invention.

FIG. 30 is a schematic representation of the components included in the implantable pump shown in FIG. 29.

DETAILED DESCRIPTION

In describing the preferred embodiments of the subject matter illustrated and to be described with respect to the drawings, specific terminology will be used for the sake of clarity. However, the invention is not intended to be limited to any specific terms used herein, and it is to be understood that each specific term includes all technical equivalents which operate in a similar manner to accomplish a similar purpose.

Referring to the drawings wherein like referenced numerals refer to like elements, there is shown in FIG. 1, in accordance with an embodiment of the present invention, a multiple reservoir implantable pump designated generally by reference number 10. Pump 10 includes upper portion 12 (best shown in FIGS. 3-6, 8, and 9) and lower portion 14, which are mechanically attached to one another. This attachment is discussed further below, but it is to be understood that while certain exemplary attachments are discussed, others may be employed in pump 10. Upper portion 12 includes three apertures 16, 18, and 20 (best shown in FIGS. 8 and 9) formed therein that partially define a lower reservoir port, an upper reservoir port, and catheter direct access port, respectively. As will be discussed more fully below, the upper and lower reservoir ports are for use in refilling the upper and lower reservoirs of the pump, while the catheter direct access port is for use in a direct injection of an active substance into the catheter (thusly bypassing other components of the pump). Lower portion 14 includes a catheter connector 22 extending therefrom (best shown in FIG. 2) as well as several sutures holes 24 suitable for receiving a suture for fixing pump 10 to a portion of the body (once again best shown in FIG. 2). Upper portion 12 also has a cap 26 attached thereto that includes apertures 17, 19, and 21 corresponding to apertures 16, 18, and 20, respectively, to partially define the lower reservoir port, upper reservoir port, and catheter direct access port noted above.

FIG. 3 depicts pump 10 having cover 26 removed therefrom so that it can be seen that upper portion 12 further includes hermetic titanium housing 28 and a valve housing 30. Further, although they are shown in other of the figures, FIG. 3 highlights a first septum 32 associated with the lower reservoir port, a second septum 34 associated with the upper reservoir port, and a third septum 36 associated with the catheter direct access port. Such septa may be of any well known construction in the art and may be formed of any suitable material, such as silicone rubber. Preferably, the septa allow for insertion of a needle therethrough during a refill or direct injection operation, and closure after removal of the needle therefrom. Septa 32 is preferably fit within aperture 16 (with aperture 17 overlying it), septa 34 is preferably fit within aperture 18 (with aperture 19 overlying it), and septa 36 is preferably fit within aperture 20 (with aperture 21 overlying it).

FIG. 4 depicts pump 10 having a top portion or housing cover of hermetic housing 28 removed therefrom. As can be seen in that drawing, housing 28 further includes a component support 38, a wall 39 surrounding and enclosing housing 28, a battery 40, a first set of pressure sensors 42 a and 42 b, and a second set of pressure sensors 44 a and 44 b. All of these components will be discussed more fully below in the discussion pertaining to the operation of pump 10. In a preferred embodiment, housing 28 includes outer portions formed of titanium. These portions, including the aforementioned top portion or housing cover are welded together so as to hermetically retain the other noted components within the housing. This is important, as several of the components are susceptible to damage if exposed to fluids within the body of a patient in which pump 10 is implanted. For instance, battery 40 and portions of pressure sensors 42 a, 42 b, 44 a, and 44 b are prone to damage if exposed to bodily fluids.

FIG. 5 is a cross-sectional view of pump 10 taken along the line A-A of FIG. 1, where it is shown that the pump also includes a lower reservoir 50, an upper reservoir 52, and a propellant chamber 54 flanked therebetween. Specifically, lower reservoir 50 is formed between a first flexible membrane 56 and a concave portion 58 of lower portion 14, while upper reservoir 52 is formed between a second flexible membrane 60 and a concave portion 62 of upper portion 12. Propellant chamber 54 is formed between and by flexible membranes 56 and 60. This is not unlike the design taught in the above-discussed '022 Publication. It is to be understood that while portions 58 and 60 are shown as being concave, any other shape is contemplated, including but not limited to, undulating shapes or the like. Moreover, FIG. 5 depicts apertures 20 and 21 and septum 36 of the catheter direct access port, as well as passages 64 a and 64 b which fluidly connect port 20 to the catheter. Thus, any active substance injected into the catheter direct access port will go directly through the catheter without passing through any of the other components of the pump. FIG. 5 also depicts a snap-fit connection 66 between cover 26 and upper portion 12, and a similar snap-fit connection 68 between upper portion 12 and lower portion 14. While snap-fit connections are indeed shown in the embodiment depicted in the figures, other connections are contemplated, including screwable connections and/or more permanent connections such as the use of adhesives, or the like. In addition, although shown as being constructed of a polymer material (e.g., PEEK), upper portion 12, lower portion 14, and cover 26 (as well as other components of pump 10) may be constructed out of metallic materials, such as stainless steel or titanium. In such a case, the different components may be connected together in different manners, such as through the use of welds or the like.

FIG. 6 is a cross-sectional view taken along line B-B of FIG. 1. Once again, lower reservoir 50, upper reservoir 52, and propellant chamber 54 can be seen in this drawing, as can flexible membranes 56 and 60. Sensors 42 a and 44 a are also shown in FIG. 6. Essentially, sensor 42 a senses the pressure of an active substance being contained in lower reservoir 50, while sensor 44 a senses the pressure of fluid being contained in upper reservoir 52. The fluid directed to these sensors may be directed as part of the dispensing operation or could be separately provided via a duct not associated with the dispensing operation. The pressure values obtained by such sensors are electronically captured by an electrical unit included in hermetic housing 28 (discussed more fully below) and utilized in varying the flow rates of active substance from pump 10. FIG. 6 also depicts a portion of micromotors 70 and 72, both of which will be discussed more fully below.

Lower portion 14 is shown in FIG. 7 separated from upper portion 12. As can be seen in that figure, a duct 74 is formed in the bottom of portion 14 in order to allow fluid to flow from passage 64 b to the catheter. Moreover, FIG. 7 depicts an interface 76 for reception of catheter connector 22. Interface 76 is essentially a cylindrical formation designed to partially house connector 22. Of course, many different configurations may be employed for both interface 76 and catheter connector 22. Likewise, it is contemplated for connector 22 or the like to be formed integral with lower portion 14 or any other portion of pump 10.

FIGS. 8 and 9 depict upper portion 12 having all other components removed therefrom, including, cover 26, hermetic housing 28, septa 32, 34, and 36, component support 38, battery 40, and sensors 42 a, 42 b, 44 a, and 44 b. Apertures 16, 18, 20, can clearly be seen, as can the entirety of valve body 30. Also shown are sensor ports 80 a and 80 b for reception of sensors 42 a and 42 b, and sensor ports 82 a and 82 b for reception of and fluid communication with sensors 44 a and 44 b are shown. These ports are essentially apertures that both hold the sensors in place and allow fluid to be directed thereto. With specific reference to FIG. 9, each of ports 80 a, 80 b, 82 a, and 82 b are shown as including an opening that allows for the active substance from different portions of pump 10 to be delivered to the sensors. Valve body 30 is also shown in FIG. 8 as including a valve aperture 84 b, with a like valve aperture 84 a on an opposite side of the valve body (not shown in FIG. 8).

Component support 38 is shown apart from the remainder of pump 10 in FIG. 10. The support includes a main body 92 that defines a battery compartment 94 for receiving battery 40, motor apertures 96 a and 96 b for receiving motors 70 and 72, respectively, slot 98 for receiving a portion of valve body 30, and guiding cylinders 100 a and 100 b (the latter of which is not shown in FIG. 10) for receiving push rods associated with the two valves included in implantable pump 10. With reference back to FIG. 4, it can be seen that component support 90 is received within a central portion of upper portion 12, so that slot 98 receives a portion of valve body 30 therein. Battery 40 is also shown disposed in battery compartment 94 in FIG. 4.

Some of the various ducts included in upper portion 12 can be seen in the cross-sectional view of FIG. 11, which is taken through line C-C of FIG. 8. The ducts are generally formed by drilling through portions of upper portion 12 and inserting glass tubes or the like. This manufacturing process may also include the closure of certain ends of the drilled channels after insertion of the tubing, for instance, through the use of core pins or the like. These ducts allow for fluid to flow from upper and lower reservoirs 50 and 52, to the above-mentioned pressure sensors and valves, as well as from the upper and lower reservoir refill ports and the catheter direct access port ultimately to the catheter (not shown). Specifically, fluid injected into the lower reservoir port enters duct 110 through a first opening 110 a and exits via a second opening/duct portion 110 b where it is ultimately led to lower reservoir 50. Likewise, fluid injected into the upper reservoir port enters duct 112 through a first opening 112 a and exits via a second opening 112 b where it is led to upper reservoir 52. As noted above, passages 64 a and 64 b facilitate fluid injected into the catheter direct access port to flow directly to the catheter (as shown in FIG. 5). FIG. 12 demonstrates where passage 64 b, second opening/duct portion 110 b and second opening 112 b are situated. Moreover, an opening is provided in duct 110 and is in communication with port 80 a (shown schematically in FIG. 15) and opening 112 a is in communication with both upper reservoir 52 and portion 82 a. Thus, the pressure of active substance flowing from lower reservoir 50 and upper reservoir 52 may be measured by sensors 42 a and 44 a, respectively.

A duct 118 is also provided and connected with duct 110. Duct 118 is preferably a capillary having a filter along at least a portion thereof. Duct 118 includes a first opening 118 a which is in fluid communication with portion 82 b and sensor 42 b, and a second portion 118 b that is in fluid communication with a first valve. Similarly, a duct 120 is also provided as a capillary having a filter along at least a portion thereof. Duct 120 is connected with duct 112 and includes a first opening 120 a that is in fluid communication with portion 80 a and sensor 44 b, and a second portion 120 b that is in fluid communication with a second valve. This allows for active substance to be directed from each of the reservoirs to the respective valves (discussed below), where the active substance flow can be varied. Specifically, fluid dispelled from lower reservoir 50 passes through opening 110 b to opening 114 where a first pressure reading can be taken by sensor 42 a. Fluid dispelled from lower reservoir 50 also travels through duct 118, where it is put into contact with sensor 42 b and ultimately passes to the first valve via second portion 118 b. Likewise, fluid dispelled from upper reservoir 52 passes through opening 112 b where a first pressure reading can be taken by sensor 44 a. Fluid dispelled from upper reservoir 52 also passes through duct 112 and into duct 120, where it is put into contact with sensor 44 b and ultimately passes to the second valve via second portion 118 b. The sensors preferably take measurements directly from each reservoir (sensors 42 a and 44 a) and just prior to entering a portion of ducts 118 and 120 that allow for a maximum flow of the fluid (sensors 42 b and 44 b). These readings can be utilized to determine the flow rate of the fluid.

FIGS. 13 and 14 depict valves 122 and 124 and their relationship to the other components of pump 10. Specifically, fluid flows to valve 122 from lower reservoir 50 by second portion 118 b and fluid flows to valve 124 from upper reservoir 52 by second portion 120 b, as is discussed above. Active substance dispelled by each of those reservoirs is introduced into the valves, which can be actuated to allow for varying of flow rate from them. Specifically, motor 70 is utilized to rotate an offset cam 126 to actuate valve 122, while motor 72 is utilized to rotate an offset cam 128 to actuate valve 124. The tapering shape of the valves means that this actuation can result in more or less blockage of the flow path of the active substance, thereby allowing for more or less flow rate from the pump.

Propellant chamber 54 preferably includes a propellant that expands under normal body temperature, such as those known in the prior art and discussed in the '022 Publication. For instance, in one embodiment, propellant chamber 54 is filled with hexafluorobutane. When pump 10 is implanted, the propellant expands thereby causing a displacement of membranes 56 and 60, which, in turn, causes an active substance contained within reservoirs 50 and 52 to be dispelled therefrom. As discussed above, an active substance housed within lower reservoir 50 flows to both sensors 42 a and 42 b, while an active substance housed within upper reservoir flows to both sensors 44 a and 44 b. The pressure readings taken by the sensors 42 a and 42 b and 44 a and 44 b are compared by a processing unit located in pump 10 (not shown) in order to calculate the flow rate based upon the pressure differential. At this point, the electrical unit can also determine if one or both of the valves should be further actuated in order to arrive at the desired flow rate from pump 10 of each active substance. This desired flow rate can be input via an external programmer as is know in the art, or could be controlled by the electrical unit itself.

FIG. 15 depicts the path by which fluid that has passed by valves 122 and 124 takes. Specifically, fluid that passes by valve 122 proceeds through a duct 123 and fluid that passes by valve 124 proceeds through a duct 125. Each of these ducts extend around the catheter direct access port and feed into a collector manifold, not unlike that shown in FIG. 28. This manifold essentially collects fluid directly injected into the catheter direct access port (via passage 64 a) and fluid from valves 122 and 124 so that such can ultimately be passed to the catheter through passage 64 b.

FIG. 16 depicts a second embodiment pump 210. Where possible, like reference numerals for like elements to that of pump 10 are utilized, with such numbers being set forth in the 200-series of numbers. Pump 210 operates in a similar manner to pump 10, albeit with some different structure being employed. Like pump 10, pump 210 includes upper portion 212 and lower portion 214, which are mechanically attached to one another. This attachment may be similar to attachment of like elements discussed above in connection with pump 10, but also may be any other suitable attachment mechanism.

Upper portion 212 includes three apertures formed therein that partially define a lower reservoir port, an upper reservoir port, and catheter direct access port, respectively. These ports also include septa 232, 234, and 236, respectively. Like in pump 10, lower portion 214 also includes a catheter connector 222 extending therefrom (best shown in FIG. 17) as well as several sutures holes 224 suitable for receiving a suture for fixing pump 210 to a portion of the body (once again best shown in FIG. 17). Upper portion 212 also has a cap 226 attached thereto that includes apertures 217, 219, and 221 corresponding to the apertures of upper portion 212, respectively, to partially define the lower reservoir port, upper reservoir port, and catheter direct access port noted above.

FIGS. 18-20 depict one portion of a three part hermetic housing included in pump 210. Specifically, those figures depict one of two housings 228 that in addition to housing 229 (discussed below) make up the hermetic housing. Housing 228 is similar to housing 28 of pump 10, but is designed so as to house the components useful in varying the flow rate of an active substance dispensed from one of the upper and lower reservoirs included in pump 210. Moreover, housings 228 do not include valves or electronic components. The former are disposed in a portion of upper portion 212, while the latter are formed in a separate hermetic housing 229 (best shown in FIG. 21). This will all be discussed further below. Each housing 228 is preferably made of titanium or other suitable material and includes a membrane 230 formed on an exterior surface thereof, which essentially overlies an aperture formed through the housing.

As is best shown in FIG. 20, disposed on the interior of the housing is a set of pressure sensors 242 and 244, a motor 270, and a valve actuation pin 272. Pin 272 is preferably moved via an eccentric (not shown) connected with motor 270. Pressure sensor 242 is designed to measure the pressure of fluid being dispelled from one of the upper and lower reservoirs, while sensor 244 is designed to measure the pressure of fluid after it has been passed through a resistor capillary and before passing through a valve (discussed below). FIG. 19 depicts a portion of sensors 242 and 244 extending below housing 228, so as to allow for the fluid to come into contact with the sensors.

FIG. 21 depicts a cross-sectional top view of pump 210, which illustrates several additional components of the pump, plus the orientation of housings 228 and housing 229. For the purposes of the below discussion, the housing associated with the lower reservoir will be labeled and referred to as housing 228 a, while the housing associated with the upper reservoir will be labeled and referred to as housing 228 b. Components of each housing will also be referred to with the ‘a’ and ‘b’ identifier. As is shown, housings 228 a, 228 b (shown with a top portion thereof removed), and 229 are situated on three different sides of pump 210. Connecting duct 231 a connects housing 228 a with housing 229 and connecting duct 231 b connects housing 228 b with housing 229, so that the electrical components housed within housing 229 can communicate with the sensors and motor disposed in each housing 228 a and 228 b.

FIG. 21 also depicts an actuation lever 233 a which is engaged with membrane 230 a on one side and with a valve 275 a on the other and an actuation lever 233 b which is engaged with membrane 230 b on one side and with valve 275 b on the other. These levers are preferably pivotable about a center point, much like a “see saw.” More particularly, lever 233 a is pivotable about a center point which includes an adjustment screw 235 a and lever 233 b is pivotable about a center point which includes an adjustment screw 235 b. These adjustment screws allow for the relationship between the valves and levers to be adjusted, which in turn allows for the fine tuning of the fluid dispelling operation. During operation, valve 275 b, which is preferably biased to an open position, is moved by lever 233 b. Specifically, operation of motor 270 b rotates the eccentric (not shown), which in turn moves pin 272. The pin in turn moves membrane 230 b, which in turn moves lever 233 b to either apply or release a force upon valve 275 b. In the preferred embodiment shown, valve 275 b is biased via an elastic element 277 b. Of course, the particular arrangements depicted are only one fashion in which the housings can be configured, and other configurations may be employed.

FIG. 22 is a cross-sectional view of pump 210 taken along the line E-E of FIG. 21, where it can be seen that pump 210 includes a lower reservoir 250 and an upper reservoir 252, and a propellant chamber 254 defined by membranes 256 and 260. This not unlike that of pump 10, and like that embodiment, variations in the design shown are contemplated. FIG. 21 also depicts the design and orientation of valve 275 b which is shown as being of a similar design to the valves included in above-discussed pump 10. However, valve 275 b (as well as valve 275 a) is situated in a vertical orientation, as opposed to the horizontal orientation depicted in pump 10. The structure and orientation of lever 233 b can also be seen in FIG. 22. Reference is made here to the above discussion pertaining to the operation of lever 233 b, and it is noted that lever 233 b may be spring actuated or the like so that it itself can bias valve 275 b in an opposite direction (i.e., downwards in the view shown in FIG. 22) absent the force provided by membrane 230 b, pin 272 b, and motor 270 b. It is to be understood that while only one set of components is discussed (i.e., those in and associated with housing 228 b), the same structure and orientation applies to the other (i.e., those in and associated with housing 228 a).

FIG. 22 also depicts an antenna assembly 290, which is shown in that figure outside of the hermetic house, but preferably is located within housing 229. The antenna assembly preferably includes a mounting 292 around which a wire or series of wires (not show) are wound. This structure is electrically coupled with other components of housing 229, so as to allow for wireless remote connection with such components. If the antenna is to be located outside of hermetic housing 229, the coupling could be via a feed-through (not shown). It is to be noted that a ferrite core could be utilized to reduce the overall size of the antenna.

FIG. 23 is another cross-sectional view of pump 210 taken along the line F-F of FIG. 21, where lower reservoir 250, upper reservoir 252, and propellant chamber 254 can once again be seen. Moreover, FIG. 23 depicts catheter direct access port 220 and a duct network 264 that directs fluid injected through port 220 directly to a collector manifold 280, as is shown in FIG. 28 and discussed further below. Manifold 280, in turn, directs directly injected fluid to catheter connector 222, and ultimately through the catheter. Moreover, a duct network 265 is shown connected to lower reservoir 250 and acts to direct fluid both from the lower reservoir port to lower reservoir 250 during a refill procedure and from lower reservoir 250 towards manifold 280, as will be discussed further below. As shown in FIG. 23, duct network 265 includes duct portions 265 a and 265 b, as well as other portions which will be discussed more fully below. FIG. 24 is another cross-sectional view of pump 210 taken along the line G-G of FIG. 21, which shows in more detail valve 275 a. As shown, silicone valve cone 276 a is provided in the valve assembly to ensure that no leakage of fluid passing around valve 275 a occurs. Preferably, the silicone is roughed so as to ensure control of very small flow rates. However, many different surface treatments may be utilized. In one method of making such a roughened cone 276 a, a mold is sand blasted in order to produce the roughened silicone components.

FIG. 24 also depicts other portions of duct assembly 265. Specifically, where FIG. 23 depicts duct portions 265 a and 265 b, FIG. 24 depicts duct portions 265 c and 265 d. Portion 265 c includes a resistor capillary 265 e, while portion 265 d directs fluid expelled from lower reservoir 250 to valve 275 b after having passed through capillary 265 e.

FIG. 25 further depicts duct network 265. Specifically, reference numeral 265 f represents an opening where portion 265 b and 265 c meet. Portion 265 d is shown to include a bend and a filter 265 g within the duct. Essentially, duct 265 c is a relatively large passage with a smaller filter 265 f placed therein. The filter preferably prevents particulates or other matter within the fluid from being directed out of pump 210. FIG. 25 also illustrates where resistor capillary 265 e is located. A center of manifold 280 can also be seen in the figure.

With regard to upper reservoir 252, a duct assembly 266 is provided and largely shown in FIG. 25. Duct assembly 266 includes a filter 266 a which is situated along the interior perimeter of the portion shown in FIG. 25. Fluid dispelled from upper reservoir 252 can preferably enter duct assembly 266 along any portion of filter 266 a. This fluid is ultimately directed to a resistor capillary 266 b and thereafter to duct portion 266 c which directs the fluid to valve 275 a. In addition, duct assembly 266 includes a duct portion 266 d which allows fluid from the upper reservoir refill port to enter upper reservoir 252 during a refill operation and a duct portion 266 e which provides fluid from upper reservoir 252 to sensor 242 a. Although not shown in FIG. 25, lower reservoir 250 is fluidly connection with sensor 242 b.

Upper portion 212 is shown in FIGS. 26 and 27 separated from all other components of pump 210. In FIG. 26, apertures 216, 218, and 220, can clearly be seen, as can sensor ports 280 a and 282 a for reception of the portion of sensors 242 a and 244 a extending below housing 228 a and sensor ports 280 b and 282 b for reception of the portion of sensors 242 b and 244 b extending below housing 228 b. Moreover, apertures 284 a and 284 b are shown and in which valves 275 a and 275 b ultimately reside. In FIG. 27, portion 265 b can be seen, as can manifold 280 (also shown in FIG. 28). In addition, FIG. 27 depicts filter 266 a and its connection to upper portion 212 via several glue spots or the like. In FIG. 28, manifold is shown separated from other portions of pump 210. As shown, the manifold operates to take three separate streams of fluid (i.e., fluid from the upper and lower reservoirs and from the catheter direct access port) and direct such to the catheter.

Operation of pump 210 is largely similar to that of pump 10, with the major differences residing in the structure to obtain that operation. The inclusion of separate hermetic housing in the design of pump 210 is beneficial from both a manufacturing and assembly standpoint. Moreover, the configuration of the valves and actuators of pump 210 allows for a hermetic sealing of only those components that are most susceptible to damage by the surrounding environment.

FIGS. 29 and 30 depict yet another embodiment pump 310. Like in pump 210, the different components of pump 310 will be referred to below with like reference numeral to that of pump 10, but within the 300-series of numbers. Pump 310 includes a central aperture 316 partially defining a refill port and a second aperture 320 partially defining a catheter direct access port. The refill port also includes a septum 332, while the catheter direct access port also includes a septum 334. The design of these septa may be like those known in the prior art, as is discussed above in connection with pumps 10 and 210.

The catheter direct access port, like in pumps 10 and 210, provides direct fluid access to a catheter connector 322. On the other hand, as is shown in FIG. 30, the refill port allows for fluid access to both a lower reservoir 350 and upper reservoir 352 (a propellant chamber 354 is shown therebetween like in the other embodiments). A programmable valve 317 is provided downstream of the refill port. This valve may be of any type known in the art or related arts and is preferably designed so as to be controllable by a medical professional or other operator during a refill procedure. For instance, valve 317 may be controlled wirelessly or via a mechanical trigger locate on the pump. Essentially, the orientation of valve 317 will dictate which reservoir is filled during a refill procedure.

The remainder of pump 310 may be similar to either of the above-discussed embodiments or even variations of each. For instance, FIG. 30 depicts two valves 375 a and 375 b, which may be designed in accordance with either the like valves of pump 10 or 210, or even in accordance with other known designs.

Although the invention herein has been described with reference to particular embodiments, it is to be understood that these embodiments are merely illustrative of the principles and applications of the present invention. It is therefore to be understood that numerous modifications may be made to the illustrative embodiments and that other arrangements may be devised without departing from the spirit and scope of the present invention as defined by the appended claims. 

1. A programmable pump system for dispensing first and second active substances at varying flow rates to a patient comprising: a pump housing defining an interior including a first chamber containing the first active substance, a second chamber containing the second active substance, and a third chamber containing a propellant; a first valve in fluid communication with the first chamber; a second valve in fluid communication with the second chamber; and a catheter fluidly connected with the first and second chambers, wherein expansion of the propellant within the third chamber causes the first active substance to flow from the first chamber at a first flow rate towards the catheter and the second active substance to flow from the second chamber at a second flow rate towards the catheter, actuation of the first valve varies the first flow rate, and actuation of the second valve varies the second flow rate.
 2. The programmable pump of claim 1, wherein the first and second active substances are identical.
 3. The programmable pump of claim 1, further comprising first and second membranes defining the third chamber.
 4. The programmable pump of claim 3, wherein the housing includes first and second portions, the first and second membranes captured between the first and second portions so that the first portion and first membrane defines the first chamber and the second portion and second membrane defines the second chamber.
 5. The programmable pump of claim 1, further comprising first and second pressure sensors associated with the first chamber and third and fourth pressure sensors associated with the second chamber, wherein a comparison of pressure readings taken by the first and second pressure sensors determines whether the first valve should be actuated and a comparison of pressure readings taken by the third and fourth pressure sensors determines whether the second valve should be actuated.
 6. The programmable pump of claim 5, further comprising a first motor for actuating the first valve and a second motor for actuating the second valve.
 7. The programmable pump of claim 6, wherein the housing includes a top plane and a bottom plane, and actuation of the first and second valves occurs in parallel planes to the top and bottom planes.
 8. The programmable pump of claim 7, further comprising a first offset cam associated with the first motor and first valve and a second offset cam associated with the second motor and second valve, wherein rotation of the first offset cam by the first motor causes the first valve to actuate and rotation of the second offset cam by the second motor causes the second valve to actuate.
 9. The programmable pump of claim 6, wherein the housing includes a top plane and a bottom plane, and actuation of the first and second valves occurs in perpendicular planes to the top and bottom planes.
 10. The programmable pump of claim 9, further comprising a first lever associated with the first motor and first valve and a second lever associated with the second motor and second valve, wherein movement of the first lever by the first motor causes the first valve to actuate and movement of the second lever by the second motor causes the second valve to actuate.
 11. The programmable pump of claim 10, wherein the first and second pressure sensors and first motor are contained within a first hermetic housing and the third and fourth pressure sensors and second motor are contained within a second hermetic housing.
 12. The programmable pump of claim 11, wherein the first and second hermetic housings are constructed of titanium.
 13. The programmable pump of claim 11, wherein the first hermetic housing includes a first aperture covered by a first membrane and the second hermetic housing includes a second aperture covered by a second membrane.
 14. The programmable pump of claim 13, wherein the first membrane is associated with the first motor and the first lever and the second membrane is associated with the second motor and the second lever.
 15. The programmable pump of claim 14, further comprising a third hermetic housing associated with the first and second hermetic housings.
 16. The programmable pump of claim 15, wherein the third hermetic housing includes at least one power source and at least one electronic element.
 17. The programmable pump of claim 1, further comprising a replenishment opening for use in filling the first chamber with the first active substance and the second chamber with the second active substance.
 18. The programmable pump of claim 17, further comprising a third valve in fluid communication with the replenishment opening and first and second chambers.
 19. The programmable pump of claim 18, wherein when the third valve is in a first position only the first chamber can be refilled and when the third valve is in a second position only the second chamber can be refilled.
 20. The programmable pump of claim 19, further comprising an actuation mechanism for actuating the third valve between the first and second positions. 